|Publication number||US6942611 B2|
|Application number||US 10/240,158|
|Publication date||13 Sep 2005|
|Filing date||27 Mar 2001|
|Priority date||1 Apr 2000|
|Also published as||DE10016422A1, DE10016422B4, DE50113634D1, EP1276520A1, EP1276520B1, US20030100816, USRE43299, WO2001074419A1|
|Publication number||10240158, 240158, PCT/2001/3467, PCT/EP/1/003467, PCT/EP/1/03467, PCT/EP/2001/003467, PCT/EP/2001/03467, PCT/EP1/003467, PCT/EP1/03467, PCT/EP1003467, PCT/EP103467, PCT/EP2001/003467, PCT/EP2001/03467, PCT/EP2001003467, PCT/EP200103467, US 6942611 B2, US 6942611B2, US-B2-6942611, US6942611 B2, US6942611B2|
|Original Assignee||Impella Cardiosystems Ag|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Referenced by (79), Classifications (14), Legal Events (7)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The invention relates to a paracardiac blood pump with a tubular housing wherein a drive unit for an impeller is housed in a longitudinally extending flow channel, the flow channel communicating with a laterally extending outlet tube.
A paracardiac blood pump is a blood pump pumping blood from a part of the heart and supplying it into the aorta or another target region, the housing of the blood pump being set against the heart outside, while the pump inlet has a direct connection to that ventricle from which the pumping is performed. From WO 97/49439, a thoracic blood pump is known. This blood pump comprises a tubular housing in which an electromotive drive unit is located. The drive unit is arranged in a flow channel in which blood flows around it. The blood is driven in a helical motion by an impeller arranged on the input side and circulates in the flow channel to leave the housing through a laterally branching outlet tube. As a whole, the blood pump with the housing and the outlet tube has an L-shaped configuration, whereby it is possible to put it to a port created on the cardiac wall while the outlet tube is connected with the target vessel. Such blood pumps serve for supporting the heart. They are put temporarily to the heart but are not totally inserted into the heart like intracardiac blood pumps known from WO 98/43688. With an intracardiac blood pump, no additional housing is provided wherein the drive unit is housed. The impeller rather supplies the blood flow without constricting it and without directing it in a well-defined manner.
It is the object of the present invention to provide a paracardiac blood pump which can be put to the heart from outside to support the heart without it being required to damage the cardiac wall by removing wall material.
This object is solved, according to the invention, with the features of claim 1. Accordingly, a cannula is arranged in front of the inlet of the pump ring, the outer diameter of said cannula being approximately as large as that of the housing containing the drive unit and the flow channel. The outer diameters of cannula and housing amount to 13 mm at maximum, preferably to 12 mm at maximum and particularly to 11 mm at maximum. The outer diameters of housing and cannula are approximately the same, which means that their tolerance amounts to 15% at most, particularly to 10% at most. At flow rates of about 4 to 6 liters per minute, an inner diameter of from 6 to 8 mm in the suction portion results in a flow velocity of less than 1.0 m/s. This flow velocity increases in the region of the impeller to 1.5 to 3.0 m/s and in the region of the annular flow channel, it decreases again to less than 1.0 m/s. On the one hand, in case of an appropriate flow guidance, such flow velocities are not so high that the blood would be damaged, and on the other hand, they are high enough to safely avoid, due to strong washing-out, dead water zones and thrombosis.
Since the blood pump is placed close to the heart, it can have a cannula of a relatively short length. By a short cannula, the flow losses in the region of the cannula are reduced, the pump being able to have a high hydraulic capacity, even with small dimensions.
In the region of the flow channel and the cannula, the pump has high flow velocities. These high flow velocities result in that all blood-carrying regions are washed out well, with the consequence that the danger of forming thrombi is reduced. This is important when the pump is used over a longer period of time (up to one month) because anticoagulants have to be used to a lesser degree. Thereby, the tendency to a postoperative bleeding and to a high blood loss can be significantly reduced.
The small flow cross sections, particularly in the region of the impeller, have the character of a fluid diode. This means that the reflux through the pump is little, preferably less than 1.0 l/min, even if the pump is at a standstill. It should even be possible to achieve such a little reflux in case of a cannulation from the atrium to the aorta where relatively high physiological pressures of from 80 to 100 mm Hg occur. Known comparable pumps, however, present retrograde flows of up to 3 l/min under physiological pressure conditions.
The blood pump according to the invention is configured such that it supplies the necessary output volume and, on the other hand, can be led through the cardiac wall such that the hole to be produced in the cardiac wall can be produced without removing material. The cannula and the housing can be pushed through a puncture site of the cardiac wall which then firmly surrounds the housing so that the pump supplies blood from the heart. When the pump is withdrawn, the cardiac wall closes again at the puncture site or it is clamped or sewn at this site. From the tip of the cannula to the branching outlet tube, the blood pump according to the invention is entirely cylindrical and of a small diameter so that it can be pushed through a puncture hole in the cardiac wall.
Preferably, the inner diameter of the branching outlet tube is about as large as that of the cannula. Thus about the same flow velocity as in the cannula appears in the outlet tube. The difference should be about 10% at most. High flow velocities in tube and cannula reduce the danger of thrombi formation even with low anticoagulency.
Preferably, the pump ring is configured so as to be cylindrical such that the impeller rotating therein produces an axial flow. This means that the flow in the region of the impeller is not radially deflected or only in a small measure so that the outer edges of the vanes of the impeller describe a cylindrical circumferential surface. Thereby, excessively high circumferential velocities in small gaps on the impeller are avoided, especially since the diameter of the pump ring and that of the impeller can be manufactured precisely and an axial attachment of the impeller does not effect a change of the gap.
According to a suitable embodiment of the invention, a pressure sensor for measuring the pressure of the blood to be pumped is provided on the housing. The signal of the pressure sensor is evaluated for detecting different operating states and/or detecting the current volume flow rate. It has been found out that a single pressure sensor is sufficient to detect the current volume flow rate. The respective pressure is unambiguously related to the flow rate. This relation can be detected by gauging. Moreover, extraordinary operating states, such as an obstruction of the blood flow on the outlet side or of the blood flow on the inlet side, can be detected by measuring the pressure.
Hereinafter, an embodiment of the invention is explained in detail with respect to the drawings.
In the Figures:
The blood pump illustrated in
The impeller 13 rotates in a cylindrical pump ring 16 the diameter of which is about the same as that of the envelope of the impeller. The running gap amounts to about 0.1 mm. This represents a good compromise between blood damage and hydraulic losses. At its front end, the pump ring 16 has an axial inlet 17 consisting here of a peripheral input bevel. The rear end of the pump ring 16 is followed by vane- and rotor-free transition region 18 wherein the diameter continuously enlarges from that of the pump ring to that of the housing portion 19 surrounding the drive unit 11. An annular flow channel 20 is formed between the wall of the housing portion 19 and the outer surface of the pump unit 11.
At the rear end of the housing 10, a holding body 21 consisting of hardened adhesive is located which fills out a recess 22 of the housing and forms a rounded projection protruding backwards and holding the rear end of the drive unit 11. The drive unit 11 thus projects from the holding body 21 in the manner of a cantilevered beam, without any lateral support.
Near the rear end of the flow channel 20, an outlet tube 23 laterally branches from the pump housing. This outlet tube 23 extends tangentially to the flow channel 20. In flow direction, its inner surface 24 enlarges in the way of a diffuser with a cone angle of 8° at most to avoid flow interruptions. A hose with even and smooth transition can be connected to the outlet tube 23.
In the region of the flow channel 20, a pressure detection opening 25 communicating with the flow channel 20 is provided on the housing wall. From the pressure detection opening 25, a pressure channel 26 leads into the lumen of a hose 27 extending through the catheter 12. At the proximal end of the catheter, a pressure sensor can be connected to detect the pressure at the place of the pressure detection opening 25. As an alternative, a pressure sensor can be installed at the pressure detection opening 25.
Alternatively, the pressure detection opening can be arranged, with axial orientation, on the rear end wall in immediate proximity of the holding body 21 or, with radial orientation, on the pump ring 16 in the region of the impeller 13.
The pressure prevailing in the flow channel 20 gives information about the current volume flow and also about particular operational conditions, such as, for example, an occlusion at the pump inlet or at the outlet. The monitoring of these parameters is effected by a single absolute value measuring of the pressure, i.e., without a differential pressure measuring.
A tubular cannula 30 mounted on the pump ring 16 extends from the housing 10. The cannula 30 has longitudinally extending slots 31 arranged so as to be peripherally distributed, and an axial opening 32 in a rounded cap 33 at the front end. The length of the cannula 30 does not exceed the length of the housing 10, the pump ring 16 belonging to the housing.
In the described embodiment, the outer diameter D1 of the housing portion 19 is 11 mm. The inner diameter D2 in the region of the flow channel 20 amounts to 10 mm. The drive unit 11 has a diameter D3 of <7.0 mm. The inner diameter D4 of the pump ring 16 amounts to 6 mm. The outer diameter D5 of the cannula 30 amounts to 10 mm and the inner diameter of the cannula amounts to 8 mm.
The mentioned dimensions result in blood flow rates of from 1.5 to 3 m/s in the region of the pump ring, from 1.0 to 1.5 m/s in the region of the flow channel 20, and of 0.5 m/s in the region of the outlet tube 23. The drive unit 11 runs at a high rotational speed of from 25,000 to 30,000 rpm. In doing so, the impeller 13 delivers 4 to 6 l (liters) of blood per minute under physiological pressure conditions.
The entire housing 10 including the pump ring 16 has a length of about 50 mm, and the portion of the cannula 30 projecting beyond the pump ring has a length of about 35 mm.
Through a puncture hole in the cardiac wall, the paracardiac blood pump is introduced into the heart in such a manner that the housing 10 sealingly closes the puncture hole while the cannula 30 is in the interior of the heart and the outlet tube 23 outside the heart. The puncture hole in the cardiac wall has been made without removing cardiac wall tissue. This facilitates the closing of the hole in the cardiac wall after the future withdrawal of the pump.
For a better axial fixing of the pump on a cardiac wall with a so-called purse-string suture, a peripheral enlargement 45 may be provided on the housing 10.
The tricuspidal valve TK is located between the right atrium RA and the right ventricle RV, and the pulmonary valve PK is located between the right atrium RA and the pulmonary artery PA. The superior vena cava OHV and the inferior vena cava UHV lead into the right atrium.
With the blood pump arranged as described above, an essential portion of the length of the housing 10 and the cannula 30 is located in the interior of the heart, while a relatively short portion of the housing projects from the heart, and the outlet tube 23 together with the hose connected therewith lies close against the outside of the heart. Therefore, the blood pump does not occupy substantial room.
The blood pump is implanted into the open heart to effect a heart support for the time of an operation or another intervention. An essential advantage consists in that no heavy-weight and voluminous pumps have to be borne on the thoracic region of the patient.
The pump is so small and light that even the fragile right or left atrium is not substantially deformed by applying and introducing the pump.
In the example illustrated in
In the example of
It can be noticed that in all cases the positioning of the pump is effected in a space-saving manner, disturbances and impairments of the access to the heart being kept as low as possible.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US5824070||30 Oct 1995||20 Oct 1998||Jarvik; Robert||Hybrid flow blood pump|
|EP0764448A2||20 Sep 1996||26 Mar 1997||United States Surgical Corporation||Cardiac support device|
|WO1997049439A1||4 Jun 1997||31 Dec 1997||Rau Guenter||Blood pump|
|WO1998043688A1||31 Mar 1998||8 Oct 1998||Impella Cardiotechnik Gmbh||Intracardiac blood pump|
|WO2000037139A1||23 Dec 1999||29 Jun 2000||A-Med Systems, Inc.||Left and right side heart support|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7828710||5 Jun 2007||9 Nov 2010||Medical Value Partners, Llc||Apparatus comprising a drive cable for a medical device|
|US7841976||23 Mar 2007||30 Nov 2010||Thoratec Corporation||Heart assist device with expandable impeller pump|
|US7905823||29 Aug 2007||15 Mar 2011||Circulite, Inc.||Devices, methods and systems for establishing supplemental blood flow in the circulatory system|
|US7927068||9 Jun 2008||19 Apr 2011||Thoratec Corporation||Expandable impeller pump|
|US7993260||10 Nov 2009||9 Aug 2011||Thoratec Corporation||Implantable heart assist system and method of applying same|
|US7998054||23 Sep 2009||16 Aug 2011||Thoratec Corporation||Implantable heart assist system and method of applying same|
|US8079948||29 Aug 2008||20 Dec 2011||NuCardia, Inc.||Article comprising an impeller|
|US8118724||4 Dec 2007||21 Feb 2012||Thoratec Corporation||Rotary blood pump|
|US8157720||26 Jan 2007||17 Apr 2012||Circulite, Inc.||Heart assist system|
|US8333686||29 Aug 2007||18 Dec 2012||Circulite, Inc.||Cannula insertion devices, systems, and methods including a compressible member|
|US8343029||23 Oct 2008||1 Jan 2013||Circulite, Inc.||Transseptal cannula, tip, delivery system, and method|
|US8371997||27 Oct 2011||12 Feb 2013||NuCardia, Inc.||Article comprising an impeller II|
|US8376707||25 Mar 2011||19 Feb 2013||Thoratec Corporation||Expandable impeller pump|
|US8388565||22 Oct 2010||5 Mar 2013||NuCardia, Inc.||Apparatus comprising a drive cable for a medical device (II)|
|US8449443||6 Oct 2009||28 May 2013||Indiana University Research And Technology Corporation||Active or passive assistance in the circulatory system|
|US8460168||9 Mar 2010||11 Jun 2013||Circulite, Inc.||Transseptal cannula device, coaxial balloon delivery device, and methods of using the same|
|US8485961||4 Jan 2012||16 Jul 2013||Thoratec Corporation||Impeller housing for percutaneous heart pump|
|US8535211||1 Jul 2010||17 Sep 2013||Thoratec Corporation||Blood pump with expandable cannula|
|US8545379||24 Jun 2008||1 Oct 2013||Circulite, Inc.||Cannula for heart chamber implantation and related systems and methods|
|US8545380||2 Mar 2009||1 Oct 2013||Circulite, Inc.||Intravascular blood pump and catheter|
|US8550975 *||27 Jul 2009||8 Oct 2013||Calon Cardio Technology Limited||Heart assist apparatus|
|US8591393||5 Jan 2012||26 Nov 2013||Thoratec Corporation||Catheter pump|
|US8597170||4 Jan 2012||3 Dec 2013||Thoratec Corporation||Catheter pump|
|US8684902||4 Dec 2007||1 Apr 2014||Thoratec Corporation||Rotary blood pump|
|US8684904||15 Aug 2013||1 Apr 2014||Thoratec Corporation||Blood pump with expandable cannula|
|US8721517||13 Mar 2013||13 May 2014||Thoratec Corporation||Impeller for catheter pump|
|US8834344||9 Sep 2013||16 Sep 2014||Maquet Cardiovascular Llc||Left and right side heart support|
|US8900060 *||29 Apr 2010||2 Dec 2014||Ecp Entwicklungsgesellschaft Mbh||Shaft arrangement having a shaft which extends within a fluid-filled casing|
|US8900115||1 Jul 2011||2 Dec 2014||Thoratec Corporation||Implantable heart assist system and method of applying same|
|US8992163||11 Jan 2013||31 Mar 2015||Thoratec Corporation||Expandable impeller pump|
|US9028392||1 Dec 2006||12 May 2015||NuCardia, Inc.||Medical device|
|US9050418||16 Jul 2009||9 Jun 2015||Heartware, Inc.||Cannula tip for use with a VAD|
|US9138518||6 Jan 2012||22 Sep 2015||Thoratec Corporation||Percutaneous heart pump|
|US9199020||1 Nov 2007||1 Dec 2015||Abiomed, Inc.||Purge-free miniature rotary pump|
|US9308302||13 Mar 2014||12 Apr 2016||Thoratec Corporation||Catheter pump assembly including a stator|
|US9327067||13 May 2013||3 May 2016||Thoratec Corporation||Impeller for catheter pump|
|US9358329||13 Mar 2013||7 Jun 2016||Thoratec Corporation||Catheter pump|
|US9364592||12 Nov 2010||14 Jun 2016||The Penn State Research Foundation||Heart assist device with expandable impeller pump|
|US9364593||14 Sep 2012||14 Jun 2016||The Penn State Research Foundation||Heart assist device with expandable impeller pump|
|US9381288||11 Mar 2014||5 Jul 2016||Thoratec Corporation||Fluid handling system|
|US9421311||13 Mar 2013||23 Aug 2016||Thoratec Corporation||Motor assembly for catheter pump|
|US9446179||13 Mar 2013||20 Sep 2016||Thoratec Corporation||Distal bearing support|
|US9486566||29 Oct 2015||8 Nov 2016||Abiomed, Inc.||Purge-free miniature rotary pump|
|US9504774 *||1 Oct 2008||29 Nov 2016||Minvasc Devices, Llc||Intraatrial ventricular assist device|
|US9512852||11 Jan 2013||6 Dec 2016||Thoratec Corporation||Rotary blood pump|
|US9572917||25 Feb 2009||21 Feb 2017||Circulite, Inc.||Devices, methods and systems for establishing supplemental blood flow in the circulatory system|
|US9675738||21 Jan 2016||13 Jun 2017||Tc1 Llc||Attachment mechanisms for motor of catheter pump|
|US9675739||21 Jan 2016||13 Jun 2017||Tc1 Llc||Motor assembly with heat exchanger for catheter pump|
|US9675740||29 Apr 2016||13 Jun 2017||Tc1 Llc||Impeller for catheter pump|
|US9717833||8 Jun 2016||1 Aug 2017||The Penn State Research Foundation||Heart assist device with expandable impeller pump|
|US20050187425 *||12 Jan 2005||25 Aug 2005||Scout Medical Technologies, Llc||Left ventricular function assist system and method|
|US20070197854 *||26 Jan 2007||23 Aug 2007||Circulite, Inc.||Heart assist system|
|US20080076959 *||29 Aug 2007||27 Mar 2008||Circulite, Inc.||Devices, methods and systems for establishing supplemental blood flow in the circulatory system|
|US20080076960 *||29 Aug 2007||27 Mar 2008||Circulite, Inc.||Cannula insertion devices, systems, and methods including a compressible member|
|US20080132747 *||1 Dec 2006||5 Jun 2008||Medical Value Partners, Llc||Medical Device|
|US20080306327 *||5 Jun 2007||11 Dec 2008||Medical Value Partners, Llc||Apparatus Comprising a Drive Cable for a Medical Device|
|US20090023975 *||24 Jun 2008||22 Jan 2009||Circulite, Inc.||Cannula for heart chamber implantation and related systems and methods|
|US20090062597 *||29 Aug 2008||5 Mar 2009||Medical Value Partners, Llc||Article Comprising an Impeller|
|US20090088597 *||1 Oct 2008||2 Apr 2009||Alpha Dev Llc||Intraatrial ventricular assist device|
|US20090112050 *||23 Oct 2008||30 Apr 2009||Circulite, Inc.||Transseptal cannula, tip, delivery system, and method|
|US20090118567 *||1 Nov 2007||7 May 2009||Thorsten Siess||Purge-free miniature rotary pump|
|US20090171137 *||2 Mar 2009||2 Jul 2009||Circulite, Inc.||Intravascular blood pump and catheter|
|US20090182188 *||25 Feb 2009||16 Jul 2009||Circulite, Inc.||Devices, methods and systems for establishing supplemental blood flow in the circulatory system|
|US20100022939 *||16 Jul 2009||28 Jan 2010||Heinrich Schima||Cannula tip for use with a vad|
|US20100249490 *||9 Mar 2010||30 Sep 2010||Circulite, Inc.||Transseptal cannula device, coaxial balloon delivery device, and methods of using the same|
|US20100249491 *||9 Mar 2010||30 Sep 2010||Circulite, Inc.||Two-piece transseptal cannula, delivery system, and method of delivery|
|US20110040140 *||22 Oct 2010||17 Feb 2011||Medical Value Partners, Llc||Apparatus Comprising a Drive Cable for a Medical Device|
|US20110106115 *||16 Jan 2009||5 May 2011||Med Institute, Inc.||Intravascular device attachment system having struts|
|US20110106120 *||16 Jan 2009||5 May 2011||Med Institute, Inc.||Intravascular device attachment system having tubular expandable body|
|US20110112353 *||20 Aug 2010||12 May 2011||Circulite, Inc.||Bifurcated outflow cannulae|
|US20110124950 *||27 Jul 2009||26 May 2011||Calon Cardio Technology Ltd||Heart Assist Apparatus|
|US20110160844 *||16 Jan 2009||30 Jun 2011||Med Institute Inc.||Intravascular device attachment system having biological material|
|US20120101455 *||29 Apr 2010||26 Apr 2012||Ecp Entwicklungsgesellschaft Mbh||Shaft arrangement having a shaft which extends within a fluid-filled casing|
|EP2650029A1||28 Aug 2007||16 Oct 2013||CircuLite, Inc.||Devices and systems for establishing supplemental blood flow in the circulatory system|
|EP2845614A1||28 Aug 2007||11 Mar 2015||CircuLite, Inc.||Devices, methods and systems for establishing supplemental blood flow in the circulatory system|
|EP2891502A1||1 Aug 2008||8 Jul 2015||CircuLite, Inc.||Cannula insertion devices, systems, and methods including a compressible member|
|EP3061472A1||27 Oct 2008||31 Aug 2016||Abiomed, Inc.||Purge-free miniature rotary pump|
|WO2009058726A1 *||27 Oct 2008||7 May 2009||Abiomed, Inc.||Purge-free miniature rotary pump|
|WO2017015476A1 *||21 Jul 2016||26 Jan 2017||Thoratec Corporation||Cantilevered rotor pump and methods for axial flow blood pumping|
|International Classification||F04D29/52, F04D3/02, A61M1/10, A61M1/12|
|Cooperative Classification||A61M1/122, A61M1/125, A61M1/1086, A61M1/127, A61M1/1029, A61M1/1008, A61M2230/30, A61M1/101|
|27 Sep 2002||AS||Assignment|
Owner name: IMPELLA CARIOTECHNIK AG, GERMANY
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:SIESS, THORSTEN;REEL/FRAME:013407/0647
Effective date: 20020507
|1 Apr 2003||AS||Assignment|
Owner name: IMPELLA CARDIOTECHNIK AG, GERMANY
Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE SPELLING OF THE ASSIGNEE ADDRESS PREVIOUSLY RECORDED ON REEL 013407 FRAME 0647;ASSIGNOR:SIESS, THORSTEN;REEL/FRAME:013902/0734
Effective date: 20020507
|1 Nov 2004||AS||Assignment|
Owner name: IMPELLA CARDIOSYSTEMS AG, GERMANY
Free format text: CHANGE OF NAME;ASSIGNOR:IMPELLA CARDIOTECHNIK AG;REEL/FRAME:015931/0653
Effective date: 20040910
|16 Oct 2007||RF||Reissue application filed|
Effective date: 20070910
|4 Mar 2009||FPAY||Fee payment|
Year of fee payment: 4
|11 Aug 2016||AS||Assignment|
Owner name: IMPELLA CARDIOSYSTEMS GMBH, GERMANY
Free format text: CHANGE OF NAME;ASSIGNOR:IMPELLA CARDIOSYSTEMS AG;REEL/FRAME:039655/0875
Effective date: 20140728
|9 Sep 2016||AS||Assignment|
Owner name: ABIOMED EUROPE GMBH, GERMANY
Free format text: CHANGE OF NAME;ASSIGNOR:IMPELLA CARDIOSYSTEMS GMBH;REEL/FRAME:039980/0592
Effective date: 20060622